|Publication number||US5103814 A|
|Application number||US 07/398,324|
|Publication date||Apr 14, 1992|
|Filing date||Aug 24, 1989|
|Priority date||Apr 28, 1988|
|Publication number||07398324, 398324, US 5103814 A, US 5103814A, US-A-5103814, US5103814 A, US5103814A|
|Original Assignee||Timothy Maher|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (2), Non-Patent Citations (4), Referenced by (131), Classifications (8), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This is a continuation of application Ser. No. 07/187,505 filed on Apr. 28, 1988, now abandoned.
This invention relates to respirators, for the ventilation of persons whose normal respiratory function is impaired.
Ventilators, or respirators, in medical practice are machines designed to assist a respiratorily impaired patient with breathing. Breathing is a complicated physiological process, but in simplified form, it is a means of delivering oxygen while simultaneously removing carbon dioxide from the tissues of the body.
This is accomplished by the interrelationship of the lungs and by blood circulation; oxygen being transported primarily in bound form in hemoglobin within the blood, and carbon dioxide being primarily transported in solution form in blood plasma.
The most exact indication of proper ventilation is obtained through means of blood gas studies, which can accurately indicate the dissolved and transported oxygen and carbon dioxide within the patient's blood. Since both oxygen and carbon dioxide are ultimately transported across tissue interfaces by diffusion, the partial pressures of the gasses in the solution are the most important criteria, as these indicate whether adequate flow of oxygen and carbon dioxide is occurring.
In a respiratorily impaired patient, a mechanical ventilator is used to augment the breathing process. With current ventilators and modern day medical practice, a number of variables are routinely controlled in order to achieve adequate ventilation of the patient. Primarily controlled variables include the percentage of oxygen in the gas delivered to the respiratory patient's lungs, the number of breaths per minute delivered to the patient, and the tidal volume or total volume of air interchanged in each delivered breath.
Secondary variables which are important in specific patients include positive end expiratory pressure (PEEP), the time of inspiration and expiration with relation to the overall cycle of the breath and the peak flow rate of gas being delivered during a breath. These latter variables may be controlled by a physician as required to overcome certain disease or injury related processes or degradations of the lungs.
When the patient is placed on a ventilator, positive gas passing to the lungs is provided either by an inserted endotracheal tube or, in some cases, by means of a tracheotomy. Depending upon the condition of the patient, various of the above controlled variables are set, the most important being the percentage of oxygen within the respiratory gas to be delivered, the number of breaths per minute to be delivered, the volume of each breath, and the amount of pressure to be maintained in the lungs after expiration (PEEP). After a patient is placed on a ventilator, there are two major goals in his treatment: the first is to decrease the percentage of oxygen in delivered gas to an acceptable partial pressure, as high oxygen percentages over a long period of time are toxic to the lungs; the second is to allow the patient to breathe for himself as much as possible, decreasing the actual mechanical breathing performed by the ventilator.
Various prior art sensors and control combinations have been suggested. Thus, Schultz, U.S. Pat. No. 4,326,513, suggests a control system within a respirator, using a sensor to directly measure the arterial partial pressure of oxygen which, in a closed loop through a mixer, mixes oxygen with other breathing gasses so as to minimize the oxygen concentration while maintaining a desired arterial oxygen partial pressure. This is limited, however, by the lack of a suitably accurate, medically approved, real time sensor for arterial partial pressure of oxygen.
U.S. Pat. No. 3,734,091 to Taplin discloses the use of a device to detect super-saturation of oxygen in the body, together with a control device which produces a temporarily anoxic (oxygen deficient) status within the user to control the oxygen concentration in the breathing mixture. The device is described as being used to maintain close to one hundred percent saturation of oxygen within the body, but is unusable in a respiratorily inhibited patient as the deliberate induction of an anoxic state in such a patient is extremely hazardous.
Separately, a number of patents have used CO2 analysis of exhaled gas to start and stop respirator action. U.S. Pat. No. 4,537,190 to Caillot discloses the use of a CO2 analysis cell within the exhaled air together with a control unit which turns the respirator on or off depending upon the level of exhaled CO2 detected.
U.S. Pat. No. 4,617,924 discloses a particular CO2 detection and controller of use in a high frequency ventilation system, disclosing an adaptation to permit final expiatory CO2 concentration to be more accurately determined when the exhaled gas may be intermingled with flush gas, to alleviate an inaccuracy otherwise inherent in high frequency ventilation systems, due to the dilution of the exhaled gasses by flush gas flow.
U.S. Pat. No. 4,016,876 to Martin discloses a breathing apparatus for a healthy user, particularly a fire fighter's breathing system, in which the amount of exhaled carbon dioxide is utilized to trigger replenishment within an air re-breathing apparatus. The device is suitable solely for control of closed cycle respirators for use by otherwise healthy personnel.
A similar, constant volume re-breathing system is shown in U.S. Pat. No. 3,951,137 to Conkle, which utilizes detection of differential pressure, by measuring the inhalation and exhalation pressure induced by respiration of the user to trigger a following effect in the respirator-breathing apparatus.
U.S. Pat. No. 4,612,928 to Tiep discloses a method of minimizing utilization of oxygen within an oxygen re-breather by using a pulse detection circuit to detect breathing cycles in the individual and by supplying oxygen only during inhalation steps.
Sensors for the monitoring of exhaled gasses are shown in U.S. Pat. No. 4,631,966 to Brugnoli and U.S. Pat. No. 4,602,653 to Ruiz-Vela.
A ventilator is shown, having automatic controls with a particular control sequence, providing a ventilator which progressively weans the patient from the necessity for mechanical ventilation, where this is possible, but that detects and maintains the patient's condition against an inability of the patient to resume normal respiration.
The ventilator utilizes sensors of proven reliability, and has a control sequence which is adapted to the particular form of the sensor concerned to insure the patient's safety, and to insure proper ventilator functioning.
The ventilator of this design progressively controls two of the major ventilator functions; percentage of oxygen in the respirated gas, and the total amount of assisted ventilation (the number of breaths per minute). Other variables, such as tidal volume of gas respirated per breath, positive end expiratory pressure, and the like, need not be automatically varied for proper respirative function, but may be set based upon the patient's physical condition and disease state at the beginning of ventilation.
The patient's respiration status is non-invasively monitored to control the patient's blood oxygen level and to determine that adequate respiration is taking effect.
No direct, non-invasive blood gas measurement techniques exist. This inventive ventilator therefore provides a particular control mechanism based upon the indirect monitoring of these psychological effects related to critical variables. Blood oxygen is controlled by ascertaining, through the use of a prior art pulse oximeter, the degree of the total body oxygen saturation. A blood oximeter is a device, well developed and known, which utilizes a light probe which measures the patient's pulse through a thin area of the skin, such as a finger or ear lobe, and in turn is able to adequately sense oxygen saturation within the patient.
Oxygen saturation is not a linear function of blood oxygen partial pressure, but is related through a complex second order relationship which reflects essentially the sensitivity of blood transport of oxygen to the minimum blood partial pressure necessary to provide for binding of oxygen to blood hemoglobin.
Blood carbon dioxide can likewise be estimated by monitoring the overall carbon dioxide level in the exhaled breath of the patient, or the end tidal CO2 ; again, this is an indirect measurement of overall partial pressure of carbon dioxide in the blood, representing as it does, a measure of the transport of carbon dioxide across the lungs, due to differential partial pressure of carbon dioxide between the blood and the lungs.
The inventive ventilator therefore utilizes the body O2 saturation level, as detected by a pulse oximeter, and the exhaled CO2 percentage as detected by an end tidal CO2 monitor to control the ventilator for a given patient to automatically adjust the ventilator to deliver correct inspired oxygen and the correct number of breaths per minute, all the while progressively weaning the patient, to the extent possible, from the necessity for mechanical ventilation, by weaning the patient down to the lowest acceptable inspired oxygen level as well as to decrease the number of breaths mechanically delivered to the patient to the lowest extent tolerable to the patient.
In order to insure that the machine is properly set up for an individual patient, and to properly calibrate the machine to the patient, an initial blood gas is taken for a given patient to determine the existing oxygen and carbon dioxide blood gas levels. Based upon this, an initial setting of all relevant parameters for the ventilation will be made based on normal medical indicia. Additionally, the machine will be set to a specified minimally acceptable oxygen saturation and to a maximally acceptable carbon dioxide level. A minimum respiratory gas oxygen percentage will be set, typically at forty to fifty percent inspired oxygen, but in any case, below the level at which long term oxygen toxicity effects occur.
The ventilator then is controlled progressively by an interrelated series of step decrease functions which act as follows.
First, the inspired oxygen percentage is decreased by fixed step amount, typically ten percent. For a period of time, the patient's oxygen saturation is monitored to determine whether it has dropped below the minimum level set point, picked to insure adequate minimum blood partial pressure of oxygen, and therefore typically at least ninety percent saturation.
If the oxygen saturation of the patient has not dropped below the minimum acceptable level, then the ventilator breath rate will be decreased by a step amount and the exhaled CO2 level monitored. Again, there is a sensible time delay between this change and stabilization of the exhaled CO2 at the new level. Provided that the exhaled CO2 level runs at or below the maximally acceptable CO2 levels set for the particular patient, reflecting the relationship between that patient's exhaled CO2 and the initial blood gas level determined for that patient upon start of ventilation, then the ventilation rate will be maintained at the new lower level and the process repeated.
For most patients the process will progress until the oxygen level has been reduced to the minimum level and the ventilation assisted breath rate has been decreased to zero, indicating that the patient is breathing on his own, in a normal manner. If, however, at any point during the process either the oxygen saturation rate decreases below the acceptable amount or the exhaled CO2 increases above the maximally accepted amount, then the ventilator will step back to the previous, higher rate and further decreases in that function will not occur.
Use of the innovative ventilator permits a safe coordinated weaning of a patient from mechanical ventilation without recurrent invasive blood gas tests and without requiring medical intervention at each progressive resetting of the ventilator while preserving at all times effective ventilation of the patient.
The invention also avoids instability problems in the prior art occasioned by failure to monitor both of the critical parameters necessary for insuring adequate ventilation, or by attempting to maintain a continuous control level while using sensors which are inherently incapable of directly measuring the essential parameter to be controlled.
FIG. 1 is a block diagram of the invention in simplified form interconnected to a patient.
FIG. 2 is typical oxygen saturation curve showing the relationship between measured oxygen saturation and actual arterial partial pressure of oxygen.
FIG. 1 shows, in block diagram form, the control system of the inventive ventilator herein described. A mechanical ventilator 2 provides a physical ventilation of a patient 20 through use of a mechanical respiratory gas pumping means 6. Respiratory means 6, a relatively large displacement, low pressure air pump, pumps periodic volumes of respiratory gas 10 through a flow means or tubing 8 to the patient 20. The gas is forcibly inspirated into the patient, typically through an endotracheal tube 22 providing direct forced respiration into the lungs 26 of the patient.
The respiratory gas 10 is a mixture of oxygen and other inert gasses in a proportion controlled for the ventilator 2 by setting an interval variable mixing means 12, which mixes controlled portions of oxygen 14 and other inert gasses 16 to proved the basic respiratory gas.
The pumping means 6 provides for a breathing pressure into the lungs 26 of the patient and a second, end respiratory pressure permitting the patient to exhale through exhalation gas flow 18.
The above mechanism is well understood in the art. In practice, such a ventilator 2 will have control means which will vary the pumping rate of the respiratory pumping means 6 so as to control typically the respiratory or breathing rate in breaths per minute, the maximum respiratory pressure during the inspiration stage, as well as the positive end expiratory pressure (PEEP), the specific timing of inspiration and expiration, the total tidal volume, as well as the peak flow rate of the respiratory gas to be delivered, and the percentage of oxygen in the gas, which establishes the partial pressure of oxygen in the breathing mixture at the lung-body interface.
When a patient 20 is placed upon a ventilator 2, gas flow is through endotracheal tube 22 placed in the patient's trachea, reaching from outside his mouth and nose, or alternatively implanted through a tracheotomy.
A blood gas test on the patient establishes the patient's initial level of blood oxygen partial pressure as well as the patient's dissolved carbon dioxide level. Using readily available medical knowledge, the ventilator may then be initially set; the most important of settings will be the percentage of oxygen to be delivered in the respiratory gas (oxygen partial pressure); the number of breaths per minute delivered by the ventilator; the volume of each breath delivered; and the amount of pressure to be maintained on the lungs after expiration (PEEP).
In general, a patient requiring respiration is in an oxygen depleted state, and initial ventilation is at a very high oxygen percentage. Long term oxygen exposure at partial pressures or percentages above fifty percent oxygen is toxic. Therefore, there are two major goals in management of a patient on a respirator. The first is to reduce the oxygen percentage, where possible, to below fifty percent in order to avoid toxicity effects to the lungs; the second is to reduce the mechanical breathing by the ventilator so that the patient will resume breathing on his own; in other words, the patient should be weaned from the ventilator.
The control variables are therefore set for initial ventilation based on the patient's size, lung function, disease state and other variables known in the medical art. After the patient has been respirated for a period of time, a blood gas is taken; that is, a blood sample is drawn and standard laboratory tests are used to analyze oxygen and carbon dioxide partial pressure within the patient's blood. The oxygen partial pressure must be maintained at a minimum level in order to insure that adequate oxygen transport to the patient's tissues occurs; this is necessary to sustain life. It is, however, important that an excessive amount of oxygen not be delivered to the tissues in order to prevent toxic effects from oxygen poisoning.
Carbon dioxide partial pressure must be maintained below a maximum level in order to avoid toxic effects from excessive carbon dioxide and additionally, as carbon dioxide levels in the blood controls the patient's respiratory function, to prevent respiratory failure. The percentage of carbon dioxide in the blood is the most sensitive indicator of the overall respiration function in the patient.
In the inventive ventilator, the patient is coupled to a provided pulse oximeter 30 which is placed upon a thin extremity, such as a finger tip or ear lobe of the patient, and which by means of light transmission, measures the overall body saturation of oxygen. Referring to FIG. 2, it should be seen that the percentage of oxygen saturated within the body is not a simple function of the blood oxygen partial pressure, but rather that the blood oxygen partial pressure rapidly increases above sixty torr for an oxygen saturation percentage of above ninety percent, but even more rapidly collapses at a point somewhat below sixty torr in terms of a decrease in body oxygen saturation. This sudden break in the curve if an effect of the hemoglobin transport mechanism, which retains oxygen at a relatively stable partial pressure until a relatively low saturation level is achieved at which point total oxygen partial pressure rapidly drops, and the patient becomes anoxic.
It should thus be apparent that a simple closed loop control based on percentage oxygen saturation is not sufficiently precise to control the blood oxygen partial pressure, as excursions above a certain percentage saturation level produce rapid and uncontrolled increases in blood oxygen partial pressure, whereas decreases below the given saturation level can rapidly lead to hypoxia, causing serious irreversible damage to the patient.
The physiological purpose of respiration is to provide adequate oxygen support to the tissues of the body, while effectively removing metabolic byproducts, especially carbon dioxide, from the tissues. Maintenance of an oxygen partial pressure only satisfies the first part of this respiratory function; it is also necessary to insure that adequate ventilation or flow of gas across the lungs occurs so as to eliminate the carbon dioxide. Additionally, it is necessary to maintain the carbon dioxide within a relatively narrow range in order for the patient's normal breathing synapses to properly function and for the patient to resume breathing where that is physiologically possible.
In a respiratorily inhibited patient, it is possible to have a patient who will be incapable of mechanically resuming breathing, but whose lung function is otherwise unimpaired and where oxygen transport will occur at normal gas pressure; this is the typical picture presented by a paralyzed patient with otherwise undamaged lungs.
It is equally possible to have a patient whose respiratory function is uninhibited but who, through disease process or lung damage, has a very low capability to transport oxygen successfully from the air to the blood. Thus, an automatic ventilator must control independently both the oxygen partial pressure and the overall respiratory flow function.
The inventive ventilator 2 provides for such a control where the sensors are indirect sensors, not directly measuring the parameters to be controlled and where the patient may be weaned where possible through the function of the ventilator.
In addition to the oximeter measuring a body oxygen saturation percentage, the ventilator is provided with an end tidal CO2 sensor 40 located within the respiratory gas flow means 8 so as to sample CO2 from exhaled respiratory gasses during the expiration portion of the overall respiratory cycle as controlled by the ventilator.
Again, this provides an indirect measure of the overall CO2 level within the lungs, but, for a specific patient having some specific given degree of lung function, once the relationship between blood gas CO2 partial pressure and expired or end tidal CO2 percentage is established, monitoring of the CO2 level can be correlated for that one point.
Therefore, the innovative ventilator 2 is provided with control means 32 which concurrently perform two tasks as follows:
Oximeter 30 measures a signal proportional to body oxygen saturation percentage. This signal is provided to Oxygen level comparison means within control means 32, which compares the measured percentage to a predetermined set point oxygen saturation percentage to determine if oxygen saturation is above said chosen minimum point level, typically chosen at about ninety percent. So long as said oxygen saturation level is maintained or exceeded, a periodic mixer control means 34 step decreases the proportion of oxygen 14 within the overall respiratory gas 6 by varying the setting of the respiratory gas mixer 12. Since any particular change in setting requires a sensible amount of time to take a physiological effect, based on the overall rate of transport of the revised oxygen mixture to the lungs through the blood stream to the tissues which are measured by the oximeter 30, the step decrease is followed by a delay function which is timed by control means 34 to allow the patient's condition to stabilize between each change. Oxygen percentage is in this manner decreased until a minimum desired setting of regulatory gas mixer 12, which may be set based on general medical considerations, is achieved or until level comparison 32 indicates that the overall body oxygen saturation percentage has decreased below the minimum set level. The latter event indicates physiological lung damage or an inability of the lungs to properly transport oxygen; the previous step decrease is then reversed and the oxygen percentage is maintained continuously at the next higher minimum step. In the inventive ventilator here described, this is accomplished without establishing an anoxic condition in the patient, as shown below.
Separately, mechanical respiratory assistance is reduced as follows. An end tidal CO2 sensor 40 measures a percentage CO2 in expired breathing gas which is compared to a pre-set maximum CO2 percentage, derived for the specific patient and representing a maximum desired CO2 blood percentage.
Basically, failure of patient self-respiration will be indicated by a rise above acceptable levels of blood dissolved carbon dioxide; this in turn will result in an increase in carbon dioxide within the exhaled gasses.
The end tidal CO2 sensor therefore provides a signal proportionate to the percentage of the CO2 in the exhaled gasses which is provided to CO2 level comparison means within control 32 where it is compared against a set maximum CO2 level. So long as end tidal CO2 is below the maximal set point, CO2 rate control 44 is step decreased, decreasing the breath rate of respirator 2 in terms of breaths per minute. A time delay is interposed between each step for stabilization of the patient's respiratory function and redetermination of a stable, new end tidal CO2. This process continues until the patient is breathing totally without mechanical assistance, or until expired and tidal CO2 exceeds the set point level. In the latter case, the previous step rate decrease is reversed, and the patient is held at the next higher mechanical breathing rate, representing the lowest assistance level achievable.
In use, the ventilator 2 would have the normal settings of the prior art respirator, but in addition, would have control settings for minimum body oxygen saturation and maximum end tidal CO2 level, and an additional setting for minimum percentage oxygen delivered in the respirated gas, all as determined medically for a specific patient.
Either the oxygen saturation can be first decreased, or the patient may first be weaned from the ventilator, by reducing mechanical respiration. Control 32 therefore has a setting to initiate either O2 reduction or breath rate reduction first; control 32 does not initiate the second function until the first has reached its end state, so as to prevent a too radical decrease in respiratory function in the patient.
In either case, at the end state of the second function, the patient is maintained in a steady state, with the minimum mechanical respiratory assistance feasible.
As an example, if a patient is initially placed in a one hundred percent oxygen level, then the ventilator control will monitor the oxygen saturation through the pulse oximeter reading. So long a the pulse oximeter shows an acceptable oxygen saturation, that is, a level greater than that preset, the ventilator control internally would decrease the amount of oxygen delivered by, as an example, ten percent at twenty minute intervals. At the end of each set period, if the controller comparison means determines that the oxygen saturation remains above the preset level, the ventilator will again decrease the inspired oxygen by the set step amount. This process will continue at the preset interval for as long as the patient's oxygen saturation remains above the level set as minimally acceptable for the patient's condition, decreasing ultimately to the minimum established percentage, typically forty to fifty percent inspired oxygen. If, during this period of step decrease, the patient's oxygen saturation falls below the pre-programmed level, then the ventilator control program will return to the previous higher percentage of oxygen at which an acceptable saturation level was achieved.
Additionally, even if the patient has been weaned in terms of mechanical respiration assistance, continuing monitoring of oxygen saturation level will permit increase of oxygen should a worsening of the patient's disease state cause the patient's oxygen saturation to fall below the acceptable level.
The process is superior to that of repeated blood gas monitoring. Referring to FIG. 2, it can be seen that a blood gas monitor which monitors oxygen partial pressure has a point of insensitivity at a critical region immediately below sixty torr oxygen partial pressure of the typical patient where major changes in the patient's oxygen saturation will occur with relatively little change in the blood gas partial pressure. At the lower end of this insensitivity region a sudden and catastrophic decrease in blood oxygen content occurs for relatively small oxygen changes. By contrast, the inventive ventilator 2, by monitoring the patient's body oxygen saturation level, can be set at an upper point of inflection in the curve shown in FIG. 2. This results in considerably increased sensitivity due to the marked decrease in oxygen saturation which occurs immediately prior to the critical decrease in blood gas level. Since the blood gas partial pressure is the critical parameter to be preserved, this closed loop monitoring technique in this invention readily detects an impending critical decrease in oxygen, yet preserves the patient from the deliberate induction of a anoxic state taught in the prior art. This monitoring and control, part of the invention, is therefore intrinsically much safer for a diseased or respiratorily inhibited patient.
Subsequent to the above oxygen decrease, the end tidal CO2 monitor provides continuous readings on expired CO2 levels which will be compared to a preset maximally acceptable CO2, individually programmed for a specific patient based on initial blood gas reading upon inception of ventilation. The size and volume of each breath would be set as in a traditional ventilator. It is part of the invention that the patient may be safely weaned by progressive, timed step decreases in the breath rate, based on the comparison on the end tidal CO2 reading to the maximally acceptable expired CO2 level preset, without the necessity for further variation of flow rate or tidal volume. Thus, the ventilator is programmed to step decrease the number of breaths given per minute, pausing and monitoring to determine that the end tidal CO2 does not exceed the maximum acceptable level pre-programmed. Typically, the step decrease would be on the order of two breaths per minute with a hold period between step decreases of thirty minutes to one hour. The decrease will continue until the patient is breathing completely on his own, and thus, the patient is able to eliminate CO2 completely on his own, as evidenced by the end tidal CO2 remaining below the maximum set point level. Alternately, the assistance rate will decrease to the point where the end tidal CO2 remains at a normal level and will stay at that level with no further decreases.
As with the oxygen monitoring, the internal control continues to monitor end tidal CO2 so that if it subsequently rises above the pre-set programmed maximum rate, the ventilator will automatically resume or increase the number of breaths until an acceptable rate is maintained. A setting will also be provided on the ventilator permitting the physician to establish a minimum number of breaths per minute below which the machine will not wean.
It is part of the invention that the control relationships as stated above permit the use of indirect sensors related to body oxygen saturation rate and to expired end tidal CO2, both of which are significantly time delayed with respect to blood gas partial pressures, and yet provides adequate and accurate control of a ventilator for maintaining a patient's blood gas partial pressures at acceptable levels during artificial ventilation, while reducing artificially induced respiration to the maximum extent possible, consistent with a patient's condition.
It should thus be apparent that the invention is limited not to the specific examples above given but rather to the broader control methodology within a respirator as declared in the claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4326513 *||Jun 30, 1980||Apr 27, 1982||Dragerwerk Ag||Patient data controlled respiration system|
|US4653498 *||May 20, 1986||Mar 31, 1987||Nellcor Incorporated||Pulse oximeter monitor|
|1||"An Optimally Controlled Respirator", IEEE Transactions on Bio-Medical Engineering, vol. BME-18, #5, Sep. 87, by Mitamura et al.|
|2||"Apparatus for the Servocontrol of Arterial Oxygen Tension in Preterm Infants", Medical & Biological Engineering & Computing, Jul. 1979, pp. 449-452, by Collins et al.|
|3||*||An Optimally Controlled Respirator , IEEE Transactions on Bio Medical Engineering, vol. BME 18, 5, Sep. 87, by Mitamura et al.|
|4||*||Apparatus for the Servocontrol of Arterial Oxygen Tension in Preterm Infants , Medical & Biological Engineering & Computing, Jul. 1979, pp. 449 452, by Collins et al.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US5203343 *||Jun 14, 1991||Apr 20, 1993||Board Of Regents, The University Of Texas System||Method and apparatus for controlling sleep disorder breathing|
|US5251632 *||Jul 9, 1991||Oct 12, 1993||Hamamatsu Photonics K.K.||Tissue oxygen measuring system|
|US5282464 *||Nov 23, 1992||Feb 1, 1994||Brain Archibald Ian Jeremy||Combined laryngeal mask and reflectance oximeter|
|US5315990 *||Nov 25, 1992||May 31, 1994||Mondry Adolph J||Method for delivering incremental doses of oxygen for maximizing blood oxygen saturation levels|
|US5365922 *||Mar 19, 1991||Nov 22, 1994||Brigham And Women's Hospital, Inc.||Closed-loop non-invasive oxygen saturation control system|
|US5385142 *||Apr 17, 1992||Jan 31, 1995||Infrasonics, Inc.||Apnea-responsive ventilator system and method|
|US5388575 *||Sep 25, 1992||Feb 14, 1995||Taube; John C.||Adaptive controller for automatic ventilators|
|US5419314 *||Dec 13, 1993||May 30, 1995||Christopher; Kent L.||Method and apparatus for weaning ventilator-dependent patients|
|US5682877 *||Apr 15, 1994||Nov 4, 1997||Mondry; Adolph J.||System and method for automatically maintaining a blood oxygen saturation level|
|US5738090 *||May 22, 1996||Apr 14, 1998||Burkhard Lachmann||Respiratory system for determining an opening pressure of a long system and maintaining the lung system open|
|US5752509 *||Jul 10, 1996||May 19, 1998||Burkhard Lachmann||Artificial ventilation system|
|US5769082 *||Jul 18, 1995||Jun 23, 1998||Perel; Azriel||Method of assessing cardiovascular function|
|US5848591 *||Jun 2, 1997||Dec 15, 1998||Dragerwerk Ag||Respirator with oxygen enrichment|
|US6131571 *||Apr 30, 1997||Oct 17, 2000||University Of Florida||Ventilation apparatus and anesthesia delivery system|
|US6192883 *||Aug 3, 1999||Feb 27, 2001||Richard L. Miller, Jr.||Oxygen flow control system and method|
|US6220245 *||Feb 3, 1999||Apr 24, 2001||Mallinckrodt Inc.||Ventilator compressor system having improved dehumidification apparatus|
|US6240919 *||Jun 7, 1999||Jun 5, 2001||Macdonald John J.||Method for providing respiratory airway support pressure|
|US6283123||Apr 20, 2000||Sep 4, 2001||Keith W. Van Meter||Hyperbaric resuscitation system and method|
|US6369422||May 1, 2001||Apr 9, 2002||Atmel Corporation||Eeprom cell with asymmetric thin window|
|US6371114||Jul 24, 1998||Apr 16, 2002||Minnesota Innovative Technologies & Instruments Corporation||Control device for supplying supplemental respiratory oxygen|
|US6463930||Jan 22, 2001||Oct 15, 2002||James W. Biondi||System for automatically weaning a patient from a ventilator, and method thereof|
|US6470885||Jan 13, 2000||Oct 29, 2002||Brent Blue||Method and apparatus for providing and controlling oxygen supply|
|US6512938||Dec 12, 2000||Jan 28, 2003||Nelson R. Claure||System and method for closed loop controlled inspired oxygen concentration|
|US6532958||Jul 25, 1997||Mar 18, 2003||Minnesota Innovative Technologies & Instruments Corporation||Automated control and conservation of supplemental respiratory oxygen|
|US6561187 *||Feb 14, 2002||May 13, 2003||Minnesota Innovative Technologies & Instruments Corporation||Control of supplemental respiratory oxygen|
|US6584973||Sep 13, 2000||Jul 1, 2003||Cardiopulmonary Corporation||Ventilator control system and method|
|US6612995||Jul 26, 2001||Sep 2, 2003||Steffen Leonhardt||Non-invasive method for optimizing the respiration of atelectatic lungs|
|US6629934||Feb 1, 2001||Oct 7, 2003||Healthetech, Inc.||Indirect calorimeter for medical applications|
|US6647983 *||Mar 6, 2001||Nov 18, 2003||The Johns Hopkins University||Low-pressure valve|
|US6668829||Sep 30, 2002||Dec 30, 2003||Cardiopulmonary Corporation||System for automatically weaning a patient from a ventilator, and method thereof|
|US6671529||Nov 27, 2002||Dec 30, 2003||University Of Miami||System and method for closed loop controlled inspired oxygen concentration|
|US6675798 *||Jan 18, 2001||Jan 13, 2004||Automed - Automatic Dosage Systems, Ltd.||Automatically regulating oxygen flow to a patient|
|US6694969 *||Sep 22, 2000||Feb 24, 2004||Instrumentarium Corp.||Method to improve oxygenation in subjects suffering impaired oxygenation|
|US6761165||Feb 23, 2001||Jul 13, 2004||The Uab Research Foundation||Medical ventilator system|
|US6997880 *||Feb 28, 2002||Feb 14, 2006||Oridion Medical 1987, Ltd.||Waveform interpreter for respiratory analysis|
|US7008380||Feb 1, 2000||Mar 7, 2006||Stephen Edward Rees||Automatic lung parameter estimator|
|US7017574||Nov 17, 2003||Mar 28, 2006||Cardiopulmonary Corporation||System for automatically weaning a patient from a ventilator, and method thereof|
|US7246618 *||Jun 20, 2002||Jul 24, 2007||Nader Maher Habashi||Ventilation method and control of a ventilator based on same|
|US7331343||Feb 20, 2003||Feb 19, 2008||Minnesota Innovative Technologies & Instruments Corporation (Miti)||Control of supplemental respiratory oxygen|
|US7334578||Mar 27, 2006||Feb 26, 2008||Cardiopulmonary Corporation||System for automatically weaning a patient from a ventilator, and method thereof|
|US7527054||May 24, 2005||May 5, 2009||General Electric Company||Apparatus and method for controlling fraction of inspired oxygen|
|US7552731 *||Nov 14, 2003||Jun 30, 2009||Remcore, Inc.||Remote control gas regulation system|
|US7753049 *||Jul 13, 2010||Remcore, Inc.||Remote control fluid regulation system|
|US7802571||Sep 7, 2004||Sep 28, 2010||Tehrani Fleur T||Method and apparatus for controlling a ventilator|
|US8365727||Nov 19, 2008||Feb 5, 2013||Carefusion 2200, Inc.||Respiratory therapy system with electromechanical driver|
|US8418693 *||Mar 13, 2008||Apr 16, 2013||Koninklijke Philips Electronics N.V.||Method and device for evaluation of spirographic and gas exchange data|
|US8428672||Apr 23, 2013||Impact Instrumentation, Inc.||Medical ventilator with autonomous control of oxygenation|
|US8499761||Jun 7, 2010||Aug 6, 2013||Remcore, Inc.||Remote control fluid regulation system|
|US8524453||Feb 9, 2007||Sep 3, 2013||The Brigham And Woman's Hospital, Inc.||Lectin complement pathway assays and related compositions and methods|
|US8528552 *||Nov 30, 2009||Sep 10, 2013||Dräger Medical GmbH||SPO2 control with adaptive linear compensation|
|US8529834 *||Oct 10, 2008||Sep 10, 2013||Haemair Ltd.||Blood/air mass exchange apparatus|
|US8573205||Jul 23, 2007||Nov 5, 2013||Intensive Care On-Line Network, Inc.||Ventilation method and control of a ventilator based on same|
|US8640699||Mar 23, 2009||Feb 4, 2014||Covidien Lp||Breathing assistance systems with lung recruitment maneuvers|
|US8640700||Mar 23, 2009||Feb 4, 2014||Covidien Lp||Method for selecting target settings in a medical device|
|US8695593||Aug 20, 2007||Apr 15, 2014||Fleur T. Tehrani||Weaning and decision support system for mechanical ventilation|
|US8695596||Jun 9, 2011||Apr 15, 2014||Oridion Medical 1987 Ltd.||Weaning from ventilation using capnography|
|US8794234||Sep 24, 2009||Aug 5, 2014||Covidien Lp||Inversion-based feed-forward compensation of inspiratory trigger dynamics in medical ventilators|
|US8857429 *||Jun 13, 2008||Oct 14, 2014||Idtx Systems, Inc.||Drug delivery and monitoring system for a ventilator|
|US8863106 *||Apr 18, 2008||Oct 14, 2014||Weinmann Gerate Fur Medizin Gmbh & Co. Kg||Method and device for updating medical apparatus|
|US8869793||May 18, 2011||Oct 28, 2014||Idtx Systems, Inc.||Compact self-contained automated MDI adapters or units for ventilators|
|US8931478||Nov 19, 2008||Jan 13, 2015||Carefusion 2200, Inc.||Patient interface assembly for respiratory therapy|
|US9198586 *||Dec 5, 2013||Dec 1, 2015||University Of Florida Research Foundation, Inc.||Methods of monitoring oxygenation by positive end expiratory pressure using photoplethysmography|
|US9216267||Oct 24, 2014||Dec 22, 2015||Idtx Systems, Inc.||Compact self-contained automated MDI adapters or units for ventilators|
|US9283339 *||May 14, 2010||Mar 15, 2016||Zoll Medical Corporation||Life support and monitoring apparatus with malfunction correction guidance|
|US9345438||Feb 24, 2014||May 24, 2016||Oridion Medical 1987 Ltd.||Weaning from ventilation using capnography|
|US20020082511 *||Feb 28, 2002||Jun 27, 2002||Ephraim Carlebach||Waveform interpreter for respiratory analysis|
|US20020195105 *||Sep 4, 2002||Dec 26, 2002||Brent Blue||Method and apparatus for providing and controlling oxygen supply|
|US20030078480 *||Nov 27, 2002||Apr 24, 2003||Claure Nelson R.||System and method for closed loop controlled inspired oxygen concentration|
|US20030106553 *||Dec 6, 2002||Jun 12, 2003||Vanderveen Timothy W.||CO2 monitored drug infusion system|
|US20030111078 *||Jun 20, 2002||Jun 19, 2003||Habashi Nader Maher||Ventilation method and control of a ventilator based on same|
|US20030145852 *||Feb 20, 2003||Aug 7, 2003||Minnesota Innovative Technologies And Instruments||Control of supplemental respiratory Oxygen|
|US20040035423 *||Feb 25, 2003||Feb 26, 2004||Platt Harry Louis||System for physiological monitoring during sleep|
|US20040159323 *||Oct 28, 2003||Aug 19, 2004||Minnesota Innovative Technologies And Instruments||Control of respiratory oxygen delivery|
|US20050051167 *||Nov 17, 2003||Mar 10, 2005||Biondi James W.||System for automatically weaning a patient from a ventilator, and method thereof|
|US20050103342 *||Nov 14, 2003||May 19, 2005||Jorczak Kevin D.||Remote control gas regulation system|
|US20050109340 *||Sep 7, 2004||May 26, 2005||Tehrani Fleur T.||Method and apparatus for controlling a ventilator|
|US20050126571 *||Nov 12, 2004||Jun 16, 2005||Jorczak Kevin D.||Remote control fluid regulation system|
|US20060174884 *||Mar 23, 2006||Aug 10, 2006||Habashi Nader M||Ventilation method and control of a ventilator based on same|
|US20060213519 *||May 26, 2006||Sep 28, 2006||Minnesota Innovative Technologies And Instruments||Control of respiratory oxygen delivery|
|US20060266355 *||May 24, 2005||Nov 30, 2006||Boaz Misholi||Apparatus and method for controlling fraction of inspired oxygen|
|US20070000494 *||Jun 5, 2006||Jan 4, 2007||Banner Michael J||Ventilator monitor system and method of using same|
|US20070044805 *||Aug 24, 2006||Mar 1, 2007||Wolfgang Wedler||Method for controlling a ventilator and ventilation device|
|US20070077200 *||Sep 30, 2005||Apr 5, 2007||Baker Clark R||Method and system for controlled maintenance of hypoxia for therapeutic or diagnostic purposes|
|US20080066752 *||Sep 20, 2006||Mar 20, 2008||Nellcor Puritan Bennett Inc.||Method and system for circulatory delay compensation in closed-loop control of a medical device|
|US20080072901 *||Jul 23, 2007||Mar 27, 2008||Habashi Nader M||Ventilation method and control of a ventilator based on same|
|US20080202524 *||Feb 28, 2007||Aug 28, 2008||General Electric Company||Setting madatory mechanical ventilation parameters based on patient physiology|
|US20080230062 *||Mar 23, 2007||Sep 25, 2008||General Electric Company||Setting expiratory time in mandatory mechanical ventilation based on a deviation from a stable condition of exhaled gas volumes|
|US20080236581 *||Mar 29, 2007||Oct 2, 2008||Borje Rantala||Method in a patient ventilating system|
|US20080236582 *||Aug 20, 2007||Oct 2, 2008||Tehrani Fleur T||Weaning and decision support system for mechanical ventilation|
|US20080271010 *||Apr 18, 2008||Oct 30, 2008||Bernd Scholler||Method and device for updating medical apparatus|
|US20080308101 *||Jun 13, 2008||Dec 18, 2008||Michael Spandorfer||Drug delivery and monitoring system for a ventilator|
|US20080314385 *||Jan 30, 2007||Dec 25, 2008||Hamilton Medical Ag||O2 - Controller|
|US20090007915 *||Jan 30, 2007||Jan 8, 2009||Hamilton Medical Ag||Apparatus for regulating a mechanical ventilation|
|US20090081079 *||Oct 10, 2008||Mar 26, 2009||Haemair Ltd.||Blood/Air Mass Exchange Apparatus|
|US20090126731 *||Nov 19, 2008||May 21, 2009||Allegiance Corporation||Patient interface assembly for respiratory therapy|
|US20090126734 *||Nov 19, 2008||May 21, 2009||Allegiance Corporation||Respiratory therapy system with electromechanical driver|
|US20090210162 *||Dec 27, 2006||Aug 20, 2009||Rikshospitalet-Radiumhospitalet Hf||Method and apparatus for estimating a pao2 value for a patient subject to extracorporeal circulation|
|US20090305306 *||Feb 9, 2007||Dec 10, 2009||Th Brigham And Women's Hospital, Inc||Lectin Complement Pathway Assays and Related Compositions and Methods|
|US20090308393 *||Dec 17, 2009||Luceros Wilfredo P||Medical diagnostic cart and method of use|
|US20100101577 *||Mar 13, 2008||Apr 29, 2010||Koninklijke Philips Electronics N.V.||Method and device for evaluation of spirographic and gas exchange data|
|US20100139659 *||Nov 30, 2009||Jun 10, 2010||Dräger Medical AG & Co. KG||Spo2 control with adaptive linear compensation|
|US20100186742 *||Jan 29, 2010||Jul 29, 2010||Impact Instrumentation, Inc.||Medical ventilator with autonomous control of oxygenation|
|US20100237265 *||Sep 23, 2010||Jorczak Kevin D||Remote control fluid regulation system|
|US20100292544 *||May 14, 2010||Nov 18, 2010||Impact Instrumentation, Inc.||Life support and monitoring apparatus with malfunction correction guidance|
|US20130125891 *||Nov 17, 2011||May 23, 2013||Patrick E. Eddy||System and method for dynamic regulation of oxygen flow responsive to an oximeter|
|US20140290657 *||Jun 12, 2014||Oct 2, 2014||Covidien Lp||Method for ventilation|
|USRE40402||Jan 25, 2006||Jun 24, 2008||Maquet Critical Care Ab||Non-invasive method for optimizing the respiration of atelectatic lungs|
|CN103893866A *||Dec 27, 2012||Jul 2, 2014||北京谊安医疗系统股份有限公司||Weaning method and weaning device for intelligent breathing machine|
|CN103893866B *||Dec 27, 2012||Jun 15, 2016||北京谊安医疗系统股份有限公司||一种智能呼吸机撤机方法及装置|
|EP0666056A1 *||Feb 7, 1994||Aug 9, 1995||Azriel Prof. Perel||Method of assessing cardiovascular function|
|EP0683683A1 *||Oct 8, 1993||Nov 29, 1995||Temple University of the Commonwealth System of Higher Education||Process control for liquid ventilation|
|EP0745402A1 *||May 24, 1996||Dec 4, 1996||Burkhard Prof. Lachmann||Arrangement for determining an opening pressure for a lung system|
|EP0753320A1 *||Jun 18, 1996||Jan 15, 1997||Lachmann, Burkhard, Prof.||Artificial ventilation system|
|EP1060755A1||Jun 18, 1996||Dec 20, 2000||Lachmann, Burkhard, Prof.||Artificial ventilation system|
|EP1187651A1 *||Jun 4, 1999||Mar 20, 2002||Dima Italia S.R.L.||Electronic oxygen regulator with memory|
|EP1499824A2 *||Jan 14, 2002||Jan 26, 2005||Automed - Automatic Dosage System Ltd.||Automatically regulating oxygen flow to a patient|
|EP1642608A1||Dec 6, 2002||Apr 5, 2006||Alaris Medical Systems, Inc.||CO2 monitored drug infusion system|
|EP1893269A2 *||May 17, 2006||Mar 5, 2008||Versamed, Inc.||Apparatus and method for controlling fraction of inspired oxygen|
|EP1974764A1 *||Mar 19, 2008||Oct 1, 2008||General Electric Company||Method in a patient ventilating system|
|EP2363163A1 *||Mar 20, 2009||Sep 7, 2011||Nellcor Puritan Bennett LLC||Device for controlled delivery of breathing gas to a patient using multiple ventilation parameters|
|WO2000044427A1 *||Jan 28, 2000||Aug 3, 2000||Steffen Leonhardt||Non-invasive method for optimizing the respiration of atelectatic lungs|
|WO2000045702A1 *||Feb 1, 2000||Aug 10, 2000||Stephen Edward Rees||Automatic lung parameter estimator|
|WO2003053503A1 *||Dec 6, 2002||Jul 3, 2003||Alaris Medical Systems, Inc.||Co2 monitored drug infusion system|
|WO2005048906A2 *||Nov 12, 2004||Jun 2, 2005||Leonard Polizzotto||Remote control fluid regulation system|
|WO2005048906A3 *||Nov 12, 2004||Nov 15, 2007||Leonard Polizzotto||Remote control fluid regulation system|
|WO2006127356A2||May 17, 2006||Nov 30, 2006||Versamed, Inc.||Apparatus and method for controlling fraction of inspired oxygen|
|WO2007041332A1 *||Sep 29, 2006||Apr 12, 2007||Nellcor Puritan Bennett Llc||Method and system for controlled maintenance of hypoxia for therapeutic or diagnostic purposes|
|WO2007075089A1 *||Dec 27, 2006||Jul 5, 2007||Rikshospitalet-Radiumhospitalet Hf||Method and apparatus for estimating a pao2 value for a patient subject to extracorporeal circulation|
|WO2008036213A2 *||Sep 13, 2007||Mar 27, 2008||Nellcor Puritan Bennett Llc||Method and system for circulatory delay compensation in closed-loop control of a medical device|
|WO2008036213A3 *||Sep 13, 2007||Jun 26, 2008||Nellcor Puritan Bennett Llc||Method and system for circulatory delay compensation in closed-loop control of a medical device|
|WO2011154948A1 *||Jun 9, 2011||Dec 15, 2011||Oridion Medical 1987 Ltd.||Weaning from ventilation using capnography|
|U.S. Classification||128/204.18, 128/204.23, 128/205.11|
|Cooperative Classification||A61M2230/432, A61M16/00, A61M2230/205|
|Nov 21, 1995||REMI||Maintenance fee reminder mailed|
|Apr 14, 1996||LAPS||Lapse for failure to pay maintenance fees|
|Jun 25, 1996||FP||Expired due to failure to pay maintenance fee|
Effective date: 19960417